TW201505670A - Matrix for the infiltration with cells - Google Patents
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Abstract
Description
本申請案係關於治療或診斷用途之細胞滲透用多孔性基質。 This application is a porous substrate for cell penetration for therapeutic or diagnostic use.
自WO2004/108810 A1已知基於生物相容聚合物所製成之多孔性基質的細胞植入。在此類基質中,孔隙內連接並具有體內細胞滲透用(例如治療)或體外細胞滲透用(例如診斷)之模板的功能。對於移植而言,此類生物可再吸收的基質具有暫時局部固定植入物的功能。 Cell implantation based on a porous matrix made of a biocompatible polymer is known from WO 2004/108810 A1. In such matrices, the pores are connected and have the function of a template for in vivo cell permeation (e.g., treatment) or in vitro cell permeation (e.g., diagnosis). For transplantation, such bioresorbable matrices have the function of temporarily localizing the implant.
在某些應用中,已知的模板尚無法完全令人滿意,尤其是其臨床效能。 In some applications, known templates are not yet fully satisfactory, especially for their clinical efficacy.
本發明的目的在於改善模板的臨床效能。 It is an object of the invention to improve the clinical efficacy of a template.
為達此目的,本發明提供一種尋常碟形模板,在此模板的一側上的一表面的平均孔隙量係小於另一側(複數側)之平均孔隙量的20%。此不對稱的結構能以植入的可存活細胞能留在模板中更久的方式而將此模板置入體內。 To this end, the present invention provides a conventional dish-shaped template in which the average pore amount of one surface on one side of the template is less than 20% of the average pore amount on the other side (complex side). This asymmetric structure allows the template to be placed into the body in such a way that the implantable viable cells remain in the template for a longer period of time.
根據另一態樣,本發明提供一種多孔性生物可再吸收的基質的製造方法,其中:一開始形成不具有孔隙形成劑的一聚合物層;在該聚合物層上形成至少兩種聚合物、該等聚合物之一者用的溶劑、及水溶性之孔隙形成劑的混合物;接著蒸發溶劑然後澆水移除孔隙形成劑。在一變化型中,於後面的兩個步驟之間可進行加壓。兩種方法皆可得到高孔隙度的聚合性基質碟,但其一側不具有孔隙或至少為孔隙較少的薄膜。儘管有此薄膜,在使用時孔隙中存在的細胞供給仍是充分的,但卻大幅降低了因為 遷移所造成的損失率。在模板具有支撐連接性組織的功能的一變化型中,連續的聚合物層可為例如固定模板用的縫合材料提供充分的強度。 According to another aspect, the present invention provides a method of producing a porous bioresorbable substrate, wherein: initially forming a polymer layer having no pore former; forming at least two polymers on the polymer layer a solvent for one of the polymers, and a mixture of water-soluble pore formers; the solvent is then evaporated and then watered to remove the pore former. In a variant, pressurization can be carried out between the next two steps. Both methods can obtain a highly porous polymeric matrix disc, but have no pores on one side or at least a film with less pores. Despite this film, the cell supply present in the pores during use is still sufficient, but it is greatly reduced because The rate of loss caused by the migration. In a variation of the template having the function of supporting a connective tissue, the continuous polymer layer can provide sufficient strength for, for example, a suture material for a fixed template.
在實施例中,多孔性基質係利用例如聚合性(甲基)丙烯酸來進行親水性塗佈。為達到此目的,進行電漿塗佈步驟然後進行無電漿之塗佈步驟,藉此達到大於一微米的所需膜層厚度。 In the examples, the porous substrate is hydrophilically coated with, for example, polymerizable (meth)acrylic acid. To this end, a plasma coating step is followed by a plasmaless coating step whereby a desired film thickness greater than one micron is achieved.
在下面之實施例敘述及申請專利範圍與圖示中提供了本發明的其他特徵。本發明並非由所述的實施例所定義,而是由隨附之申請專利範圍的範疇所界定。尤其,可以下列實例以外的數目與組合來施行本發明之實施例的獨立特徵。在下面的實施例的解釋中,參考顯示了根據本發明之方法之流程圖的附圖。 Further features of the present invention are provided in the following description of the embodiments and the claims and claims. The invention is not defined by the described embodiments, but is defined by the scope of the appended claims. In particular, independent features of embodiments of the invention may be implemented in numbers and combinations other than the following examples. In the explanation of the following embodiments, reference is made to the accompanying drawings showing a flow chart of the method according to the invention.
S1‧‧‧製造無孔隙或較少孔隙之聚合物層 S1‧‧‧Manufacture of polymer layers with no or less pores
S3‧‧‧形成兩種聚合物、固體孔隙形成劑、聚合物用之溶劑的一混合物層 S3‧‧‧ A mixture of two polymers, a solid pore former, and a solvent for the polymer
S5‧‧‧蒸發溶劑 S5‧‧‧ Evaporation solvent
S7‧‧‧澆水以移除孔隙形成劑 S7‧‧‧ watering to remove pore formers
圖1為根據本發明之方法的流程圖。 Figure 1 is a flow chart of a method in accordance with the present invention.
在一主要的應用中,提供植入功能性細胞用的基質,此類細胞例如是肝細胞及/或胰島細胞。此類具有生物化學性功能的細胞會黏附在泡沫狀基質之孔隙的內壁(黏附率超過80%,或者適當塗佈時會超過95%)且在理想情況下可隨著基質被移植至細胞捐贈者本身的細胞間皮囊(mesothelial pockets)中。在此處發現,在此情況中並未發生排斥反應但只有較輕微的外來物剌激,這對於治療處理是尤其有利的。在數週內,基質被血管化且被植入的細胞不再只仰賴擴散性的供給。基質被特別配置俾使較少孔隙(或無孔隙)側向內而較多孔隙側向外,以將因遷移所造成的損失率維持在低位準。同時,一部分的可再吸收的基質逐漸發生再吸收(在3-4個月內,或至少2及/或小於7個月內)且生理環境藉此受到影響而類似地有利於治療成功。一般期望聚合物混合物的一部分能更緩慢地腐蝕(降解時間的比例至少是5)並維持長時間例如2.5-3年(或至少2年及/或少於5年)的結構完整。此類聚合物係較佳地基於α-羥基碳酸,如乳酸及/或甘醇酸(如PLA或PLGA)。被認證能用於人體之此類聚合物的製造者指出於此處具有重大意義之額定降解時間(nominal degradation times)。 In a major application, a matrix for implanting functional cells, such as hepatocytes and/or islet cells, is provided. Such biochemically functioning cells adhere to the inner walls of the pores of the foamy matrix (adhesion rate exceeds 80%, or over 95% when properly coated) and ideally can be grafted to the cells along with the matrix The donor's own cell mesothelial pockets. It has been found here that no rejection occurs in this case but only a slight foreign matter is stimulated, which is especially advantageous for therapeutic treatment. Within a few weeks, the matrix is vascularized and the implanted cells no longer rely solely on diffusive supplies. The matrix is specifically configured such that less pores (or no pores) are laterally inward and more pores are outwardly outward to maintain a low level of loss due to migration. At the same time, a portion of the resorbable matrix gradually reabsorbs (within 3-4 months, or at least 2 and/or less than 7 months) and the physiological environment is thereby affected to similarly favor treatment success. It is generally desirable that a portion of the polymer mixture be more slowly corroded (the ratio of degradation time is at least 5) and maintain structural integrity for extended periods of time, such as 2.5-3 years (or at least 2 years and/or less than 5 years). Such polymers are preferably based on alpha-hydroxycarbonic acids such as lactic acid and/or glycolic acids (such as PLA or PLGA). Manufacturers of such polymers that are certified for use in the human body point to nominal degradation times that are of great significance here.
如上所述,在塗佈過的基質上觀察到尤其良好的黏附率,即一開始在PECVD/CVD之組合處理中受到薄PAA-層(例如20-30nm)電漿塗佈接著在無電漿的作用下受到較厚的PAA-層(例如20-30μm)塗佈的基質。此較上層形成結晶態的親水層。 As noted above, a particularly good adhesion rate was observed on the coated substrate, initially in a combined treatment of PECVD/CVD by a thin PAA-layer (eg 20-30 nm) plasma coating followed by no plasma. A substrate coated with a thicker PAA-layer (eg, 20-30 μm) under action. This upper layer forms a crystalline hydrophilic layer.
一開始,將所用之已經醫藥用途認證之聚合物中之一者在氯仿中所形成的溶液倒到模具中,在45°-65℃的溫度下蒸發溶劑。接下來,混合具有預定粒子尺寸分佈的聚合物混合物與類似地具有預定粒子尺寸分佈之岩鹽顆粒,然後與在氯仿中之聚合物中之一者的溶液混合,接著將上述混合物帶到已存在的聚合物層上方。在稍微高的溫度(45℃-65℃)從此預形成物蒸發溶劑,若有需要可對其加壓使其緊密結實。對此預形成物澆水以移除鹽,藉此提供期望的孔隙度。但在本文中,一開始製造的聚合物層仍然維持無孔隙。根據使用的領域,具有較少孔隙之膜層的厚度可藉由初始溶液的量與濃度來加以控制。例如,若溶液的濃度低(例如在氯仿中4%之可緩慢降解的聚合物)且填充程度小(例如0.1-1mm如0.3mm),則可獲得極薄的薄膜。在期望獲得機械耐受度較高的結構時,可在相同的濃度下將填充程度設定得較高(例如5-50mm,通常是20-25mm)。在此情況下氯仿的蒸發從而需要較長時間(1.5小時)。在前者的情況下所得薄膜具有約10-20μm的厚度,在後者的情況下所得薄膜具有約0.5-1mm的厚度。 Initially, a solution of one of the polymers used for medical use certification in chloroform was poured into a mold, and the solvent was evaporated at a temperature of 45 to 65 °C. Next, a polymer mixture having a predetermined particle size distribution is mixed with a rock salt particle similarly having a predetermined particle size distribution, and then mixed with a solution of one of the polymers in chloroform, and then the above mixture is brought to an existing one. Above the polymer layer. The solvent is evaporated from the preform at a slightly elevated temperature (45 ° C - 65 ° C) and pressurized if necessary to make it compact. This preform is watered to remove salts, thereby providing the desired porosity. However, in this paper, the polymer layer initially manufactured remains unpored. Depending on the field of use, the thickness of the film layer with less porosity can be controlled by the amount and concentration of the initial solution. For example, if the concentration of the solution is low (for example, 4% of the slowly degradable polymer in chloroform) and the degree of filling is small (for example, 0.1-1 mm such as 0.3 mm), an extremely thin film can be obtained. When it is desired to obtain a structure with a high mechanical tolerance, the degree of filling can be set higher at the same concentration (for example, 5-50 mm, usually 20-25 mm). In this case, evaporation of chloroform takes a long time (1.5 hours). In the former case, the obtained film has a thickness of about 10 to 20 μm, and in the latter case, the resulting film has a thickness of about 0.5 to 1 mm.
成層混合物的岩鹽顆粒(中位數落在350-370μm)比聚合物粒子(可較緩慢降解之聚合物的中位數落在210μm至230μm之間,可較快速降解之聚合物的中位數落在150μm至170μm之間)略粗。鹽或總聚合物的分佈寬度(5%/95%)是類似的,即約±85-95μm。分佈的形狀可能是雙峰或三峰。成層混合物的組成約為96%鹽、1-1.5%固體聚合物及約3-5%溶解聚合物,其中固體與液體的體積比例是大約相等的。總計,可較快降解之聚合物的部分只佔聚合物的約5-20%。孔隙形成層的總厚度為5-6mm。在具有更穩定初始層的變化型中,可選擇略粗的鹽(中位數約介於400-420μm)。在此情況中,孔隙形成層的總厚度為4-5mm且可免除加壓結實的步驟。澆水持續約24小時,然後在45-50℃的溫度下乾燥。當形成塗層時,基質係設置於孔隙較少的一側,是以主要塗佈開放孔隙側。 The layered mixture of rock salt particles (median falling at 350-370 μm) is lower than the polymer particles (the median of the more slowly degradable polymer falls between 210 μm and 230 μm, and the median of the polymer that can be more rapidly degraded falls at 150 μm Slightly thicker to between 170 μm. The distribution width (5%/95%) of the salt or total polymer is similar, i.e., about ±85-95 μm. The shape of the distribution may be bimodal or trimodal. The composition of the layered mixture is about 96% salt, 1-1.5% solid polymer, and about 3-5% dissolved polymer, wherein the volume ratio of solid to liquid is about equal. In total, the portion of the polymer that degrades faster is only about 5-20% of the polymer. The total thickness of the pore-forming layer is 5-6 mm. In variations with a more stable initial layer, a slightly coarser salt (median between about 400-420 μm) can be selected. In this case, the total thickness of the pore-forming layer is 4 to 5 mm and the step of pressurizing and solidifying can be dispensed with. The watering is continued for about 24 hours and then dried at a temperature of 45-50 °C. When the coating is formed, the matrix is disposed on the side with less voids, with the predominantly open open pore side.
本文中所用的聚合物例如是自Evonik所販售者,其名稱分 別是L210s、L210、L09s、L207s、L206s(可較慢降解之PLGA-聚合物)或RG502、RG502H、RG505(可更快降解之PLGA-聚合物)。 The polymers used herein are, for example, those sold by Evonik, the names of which are These are L210s, L210, L09s, L207s, L206s (PLGA-polymers that can be slowly degraded) or RG502, RG502H, RG505 (PLGA-polymers that can degrade faster).
在體外的應用中,根據本發明的基質可具有固定會曝露至生物反應器中之藥劑之細胞的功用。例如,在此方式下,可研究選定細胞類型是否會回應所研究的藥物,可以根據藉此所獲得的觀察結果來規劃治療。類似地,因為在早期便識別了任何毒性,因此可簡化藥物的發展。 In in vitro applications, the matrix according to the invention may have the function of immobilizing cells of the agent that will be exposed to the bioreactor. For example, in this manner, it can be investigated whether the selected cell type will respond to the drug being studied, and the treatment can be planned based on the observations obtained thereby. Similarly, since any toxicity is recognized at an early stage, the development of the drug can be simplified.
S1‧‧‧製造無孔隙或較少孔隙之聚合物層 S1‧‧‧Manufacture of polymer layers with no or less pores
S3‧‧‧形成兩種聚合物、固體孔隙形成劑、聚合物用之溶劑的一混合物層 S3‧‧‧ A mixture of two polymers, a solid pore former, and a solvent for the polymer
S5‧‧‧蒸發溶劑 S5‧‧‧ Evaporation solvent
S7‧‧‧澆水以移除孔隙形成劑 S7‧‧‧ watering to remove pore formers
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